Introduction
Diabetes leads to abnormalities in cardiac relaxation that predominantly results in heart failure with preserved ejection fraction (HFpEF) [
1]. The number of comorbidities in patients with HFpEF is higher, and the clinical outcomes are worse as compared with those found in patients with heart failure with reduced ejection fraction (HFrEF) [
2‐
4]. Left ventricular diastolic dysfunction (DD) has been recognized as the pathophysiological cornerstone of HFpEF. Diffuse myocardial fibrosis and extracellular matrix remodeling may be the major causes of DD [
5,
6]. However, the early detection of diffuse fibrosis at different severity levels of DD in diabetes with HFpEF has not been fully investigated.
Cardiac magnetic resonance (CMR) T1 mapping has been used for the assessment of diffuse myocardial fibrosis. However, post-contrast T1 mapping is affected by the agent dose, the measurement timing, and the renal clearance rate. Although native T1 has recently emerged as a non-contrast imaging technique for the assessment of myocardial fibrosis [
7,
8], the corresponding change in native T1 to different quantities of fibrosis appears to be limited. In contrast, extracellular volume fraction (ECV) is not affected by many external factors, thus permitting more accurate comparisons for diffuse myocardial fibrosis quantification [
9]. Meanwhile, an endogenous contrast technique known as
native T1ρ mapping has been used for myocardial fibrosis detection [
10,
11]. In one study, a positive correlation between T1ρ and ECV was observed in 20 patients with dilated cardiomyopathy [
12]. In addition, to improve the sensitivity of T1ρ mapping for myocardial fibrosis assessment, T1ρ dispersion contrast has been adopted [
13,
14]. There is a real need for non-contrast techniques for patients with renal dysfunction or for whom contrast is otherwise contraindicated [
15].
Rhesus monkeys with spontaneous type 2 diabetes mellitus (T2DM) demonstrated manifestations that are highly similar to those of human beings [
16]. This animal model provides a unique opportunity to investigate the mechanisms of complications that arise from T2DM.
In this initial study, rhesus monkeys with T2DM and varying degrees of DD were used for diffuse myocardial fibrosis detection. We used ECV as an imaging marker to determine diffuse myocardial fibrosis content. In addition, the potential of non-contrast T1ρ mapping for the assessment of diffuse myocardial fibrosis was also explored.
Discussion
Diffuse myocardial fibrosis in monkeys with T2DM and DD was detected with the use of CMR. Monkeys with T2DM exhibited increased ECV, T1ρ, and mFI values, which may be indicative of the expansion of extracellular volume and the deposition of excessive collagen. A moderate correlation between mFI and ECV (an established surrogate marker of diffuse myocardial fibrosis) was observed. A relatively strong association between imaging markers of diffuse myocardial fibrosis (i.e., mFI and ECV) and diastolic function indicators was also observed.
In this study, rhesus monkeys with spontaneous T2DM were used. This non-human primate (NHP) model shares metabolic and pathological features with humans [
18]. Li Gong et al [
16] reported the classification and diagnosis of T2DM in the rhesus monkey subspecies
Macaca mulatta lasiotis, which was used in the present study. Like humans, the NHPs have an increased likelihood of developing obesity and T2DM with increasing age [
25]. Monkeys in this study lived in a highly controlled and stable environment, and their metabolic histories were well documented. The use of this model is critical for pharmaceutical companies to develop and test drugs. Before this model can be used appropriately, the cardiovascular complications that develop in these animals need to be well characterized. Non-invasive imaging methods allow for the longitudinal monitoring of therapeutic effects; however, the ground truth confirmation of disease must be obtained during the last stages of these monkeys’ lives.
The methods used in our study to measure diastolic function were based on well-established echocardiographic techniques. The echocardiography findings presented in this study only demonstrated DD in monkeys with T2DM. These results concurred with the findings of the studies by Can [
21] and Haihua [
26] in diabetic monkeys. The classification of DD in our study is based on our coworkers’ previous study as well as data from humans [
20,
21]. Sedated monkeys were tested under stable conditions to alleviate motion problems. A new and sensitive indicator—the GSrL, which was based on CMR cine sequences [
27]—was also used in diastolic function measurement. The GSrL was observed to be decreased in patients with T2DM as compared with lean or obese controls [
28,
29]. In our study, the GSrL in monkeys with T2DM was also lower.
DD in T2DM with HFpEF is manifested as impaired relaxation and decreased diastolic chamber compliance [
30]. Collagen deposition around intramural cardiac vessels and between myofibers as well as expanded extracellular space is thought to be important contributors to DD in the presence of T2DM [
31]. In our study, both ECV and mFI were correlated with E’ and GSrL. Su and colleagues [
32] studied patients with HFrEF and patients with HFpEF, and those authors found that ECV correlated well with peak filling rate, which is a diastolic functional index assessed by cine, only in patients with HFpEF. This again suggests that diffuse fibrosis is a key factor in the pathophysiology of DD.
As has been demonstrated in previous studies in humans [
33,
34], ECV values in monkeys with T2DM were elevated. The use of T1ρ contrast to assess myocardial fibrosis has been reported in several swine studies in which T1ρ values as much as doubled in the myocardial scar tissue as compared with the normal tissue [
10,
13]. In our study, non-contrast T1ρ values were found to increase in monkeys with T2DM as compared with HCs, but there was no significant difference between animals with mild DD and animals with moderate DD. However, mFI values were significantly different between animals with mild DD and animals with moderate DD as well as between HCs and animals with mild DD. A recent animal study [
14] provided additional evidence that mFI has a greater sensitivity for detecting diffuse types of myocardial fibrosis as compared with T1ρ in dogs with myocardial infarction.
Despite the performance of a few studies in ex vivo tissue, in vivo animals, and human patients [
11,
13,
35], the precise mechanisms by which T1ρ detects myocardial fibrosis remain unknown. The chemical exchange of γB
1 on a time scale or in an intermediate exchange regimen is likely to play an important role in the modulation of T1ρ signals [
36]. In accordance with the chemical exchange theory [
37], an increased concentration of water protons bound to macromolecules (e.g., collagen) leads to increases in mFI. The magnitude of the increase is modulated by the chemical shifts and exchange rates of the macromolecules. The higher sensitivity of mFI to the changes in collagen content may be due to the cancelation of intrinsic T2, thereby resulting in an amplified effect of the chemical exchange during the relaxation times, when water protons to exchange are locked without dephasing [
14]. It was noted previously that mFI represents the subtraction of two T1ρ images. In theory, mFI cannot have a value of zero due to the presence of collagens. However, as a result of the noise in the measurement, the values of mFI in normal myocardial tissue can be close to zero.
Although a good correlation between mFI and ECV was found, there were still differences. The precise mechanisms that account for the different behaviors of ECV and mFI and that allow them to differentiate HCs from animals with mild DD remain unknown. One reason may be that increased ECV reflects the expansion of extracellular volume whereas increased mFI reflects the deposition of excessive collagen. In a recent study by Shiro and colleagues [
38], ECV was strongly correlated (
r = 0.86) with the histological extracellular space component but only modestly correlated (
r = 0.66) with the histological collagen volume fraction in patients with dilated cardiomyopathy. Future studies to systematically validate the mFI method with the use of histologically defined collagen volume are warranted, and they should include a sufficient sample size. Meanwhile, the relationship between collagen deposition and extracellular volume expansion is still in need of further investigation.
Limitations
Due to the use of this rare, naturally occurring, chronic, NHP disease model of monkeys with T2DM as well as the longitudinal long-term study consideration, only one monkey with T2DM and DD was sacrificed for histopathology to show diffuse myocardial fibrosis. The ECV measurements in this study had not previously been validated in a monkey model. Given the close agreement of ECV among various species [
39,
40], it is reasonable to assume that the ECV measurement in a monkey is still valid, although direct rigorous validation remains to be performed by histopathology. While we did monitor blood pressures immediately before and after CMR study, we did not have pressure data during the CMR study to normalize CMR results. This limitation will be resolved with the addition of MRI-compatible physiological monitoring at our institute [
41]. Finally, although there are statistically significant differences in ECV and mFI between the different monkey groups, there is also an overlapping of values. Further studies with larger simple sizes are needed for vigorous validation beyond this initial investigation.
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